Urine Flow Monitoring Device and Method

ABSTRACT

Unique characteristic sounds produced as urine impacts the surface of the water are used to monitor men&#39;s urinary flow patterns and their dynamics. By detecting the intensity at selected acoustic frequencies, it is possible to accurately and precisely measure the urine flow rate. Techniques for analyzing urine flow and its dynamics employ sound levels that are detected with digital filters at two or more distinct frequency regions or channels of the sound spectrum. One frequency region that is designated the measurement channel is where the sound measurement intensity strongly depends on urine flow levels. Another frequency region that is designated the reference channel is where the sound measurement intensity is not dependent on urine flow levels. By using a combination of measurements from the measurement channel and the reference channel, the urine flow monitoring apparatus compensates for variations in operating conditions and other factors during use.

REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part application of applicationSer. No. 12/877,289 that was filed on Sep. 8, 2010 and claims priorityto U.S. provisional application 61/353,216 that was filed on Jun. 10,2010.

FIELD OF THE INVENTION

The present invention generally relates to a medical apparatus formonitoring the discharge of urine by an individual. The apparatus gaugesthe volumetric flow and flow dynamics of the discharge, analyzes thedata and displays the results.

BACKGROUND OF THE INVENTION

The prostate is a gland of the male reproductive system that is locatedin front of the rectum and just below the bladder. The prostate,comprised largely of muscular and glandular tissue, is wrapped aroundthe urethra, which carries urine from the bladder out through the tip ofthe penis. Disorders of the prostate are fairly common during the agingprocess and include prostatitis, benign prostatic hyperplasia (BPH), andadenoma of the prostate, or prostate cancer. Prostatitis, which may ormay not be the result of an infection, is generally defined as aninflammation of the prostate. Symptoms associated with prostatitis arepain, voiding symptoms such as nocturia, frequency and urgency ofurination, incomplete voiding, and decreased force and/or intermittencyof the urinary stream, impotence, and infertility.

Benign prostatic hyperplasia (BPH) is a noncancerous enlargement of theprostate and is common in men over age 40. Symptoms associated with BPHare similar to those observed with prostatitis. Prostate cancer, i.e.,adenocarcinoma of the prostate, is the most common malignancy in mengreater than 50 years in the US. The incidence increases with eachdecade of life. Prostate cancer is generally slowly progressive and maycause no symptoms. In late disease, symptoms of bladder outletobstruction, urethral obstruction, and hematuria may appear andmetastasis to the bone may occur.

Diagnosis of urological disorders is often facilitated by a patient'surine flow rate data. Urological disorders such as an obstruction in thelower urological tract or neurotic bladder can be detected by studyingthe patient's urine flow rate as it varies from the beginning of voidingto the end and the total volume of urine voided. This data can becompared to the mean data for an individual of the same sex and age tohelp determine the degree of urethral stricture.

Urine flow data is also useful in diagnosing prostrate enlargement.Prostrate enlargement usually occurs gradually with no noticeableimpairment to the patient. Merely observing the patient void willusually not enable the urologist or physician to accurately assess thedegree of prostate enlargement. However, by observing histograms of theurine flow, the urologist or physician can usually detect the degree ofprostrate enlargement and the necessary procedures to be undertaken tocorrect the disorder. In addition, post-operative urine flow dataprovides an excellent way of assessing the benefit achieved by surgery.

A variety of urine flow meters for providing urine flow data arepresently commercially available. For example, mechanical urine flowmeter devices usually comprise a container having a graduated scale forindicating the volume of urine within the container. Urine flow isdetected by observing the change in volume as the patient voids into thecontainer. Electrical urine flow meters for providing urine flow datahave been developed. These devices may have a urine velocity-measuringapparatus in the form of a urine flow receptacle with a paddle wheeljournaled therein. The paddle wheel is mechanically linked to agenerator, which produces an output voltage, which is displayed on avoltmeter. The velocity of the urine stream impinging on the paddlewheel determines the paddle wheel velocity and therefore the outputvoltage of the generator. Other urine flow devices include aurine-receiving receptacle that has a pair of parallel spaced-apart rodsor strips disposed therein. The rods or strips are electricallyconnected to a capacitance sensing circuit. As the volume of urinewithin the receptacle increases, the capacitance between the rods alsoincreases so that by measuring the rate of change of the capacitance, anindication of the urine flow may be obtained.

As is apparent, current urine flow meters are complex and often requirethe assistance of a clinician for proper use; moreover, the devicesrequire a high degree of maintenance. Furthermore, since urine contactscomponents in each of the meters, those components must be cleanedfollowing each use. Therefore, a need exists for a reliable, lowmaintenance urine flow meter.

SUMMARY OF THE INVENTION

The present invention is based in part on the recognition that duringurination (or voiding process) the unique characteristic sounds that areproduced by the urine as it impacts the surface of the water in a toiletor urinal can be used to monitor the person's urinary flow pattern andits dynamics. Specifically, because the sound's intensity (loudness) andspectrum depend on the urine flow level, by detecting the intensity atselected acoustic frequencies, it is possible to accurately andprecisely measure the urine flow rate.

In a preferred embodiment, the present invention is directed totechniques for analyzing urine flow and its dynamics by using soundlevels that are detected at two or more distinct frequency regions orchannels of the sound spectrum. One frequency region that is designatedthe measurement channel is where the sound measurement intensity oroutput strongly depends on urine flow levels. Another frequency regionthat is designated the reference channel is where the sound measurementintensity is not dependent on urine flow levels. By using a combinationof measurements from the measurement channel and the reference channel,the urine flow monitoring apparatus of the present invention compensatesfor variations in operating conditions and other factors during use.

In one aspect, the invention is directed to an apparatus for measuringurine flow that includes:

a microphone for detecting acoustical sound that is generated as urineimpacts a liquid surface and converting it into electrical signals;

an amplifier operatively coupled to the microphone to amplify electricalsignals therefrom;

an analogue-to-digital converter for converting electrical signals intodigital form;

a digital filter operatively connected to the analogue-to-digitalconverter for extracting filtered signals; and

a signal processor for analyzing filtered signal components to generateurine flow level data.

In another aspect, the invention is directed a device for measuringurine flow that includes:

a transducer for detecting acoustical sound that is generated as urineimpacts a liquid surface and converting it into electrical signals;

an amplifier to amplify the electrical signals;

an analogue-to-digital converter for converting the electrical signalsinto digital form;

a digital filter for extracting filtered signals; and

means for analyzing signal components to generate urine flow level data.

In a further aspect, the invention is directed to a system for analyzingurinary flow patterns of a male patient as he voids that includes:

a transducer for converting acoustic energy, that is generated as urinefrom the patient impacts a surface, into electrical signals;

an amplifier operatively coupled to the transducer to amplify electricalsignals therefrom;

an analogue-to-digital converter for converting the electrical signalsinto digital form;

a digital filter operatively coupled to the analogue-to-digitalconverter for extracting filtered signals; and

means for analyzing signal components to identify urinary flow patterns.

In yet another aspect, the invention is directed to a portable apparatusfor measuring urinary flow patterns that includes:

(a) an audio peripheral that includes:

-   -   a transducer for converting acoustic energy, that is generated        as urine from a patient impacts a surface, into electrical        signals; and    -   an amplifier operatively coupled to the transducer to amplify        electrical signals therefrom;

(b); an analogue-to-digital converter for converting the electricalsignals into digital form;

(c) a processing peripheral that includes:

-   -   a digital filter operatively coupled to the analogue-to-digital        converter for extracting filtered signals; and    -   means for processing signal components to generate signals that        are representative of urinary flow data, wherein the        analogue-to-digital converter is housed in the audio peripheral        or in the processing peripheral.

In a still another aspect, the invention is directed to a method formeasuring urinary flow from a male patient as he voids that includes thesteps of:

(a) detecting acoustic energy that is generated as urine impacts aliquid surface;

(b) converting the acoustic energy into electrical signals;

(c) extracting filtered signals from the electrical signal with adigital filter; and

(d) processing the filtered signals to generate output signals thatrepresent urinary flow data for the male patient.

In a preferred embodiment of the urine flow-monitoring device yieldsurine flow data that is selected from the group consisting of averageflow rate, maximum flow rate, time to maximum flow level, flow dynamics,and combinations thereof.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1 to 8 are schematics of alternative configurations of the urineflow monitoring device;

FIG. 9 illustrates the operations of a urine flow monitoring devicetransmitting data;

FIG. 10 is a graph of sound spectra (loudness in decibel vs. frequency)that are generated by the impact of urine on water;

FIG. 11 shows the measured output signals from the measurement channeland two reference channels vs. time from a urine flow monitoringapparatus in detecting sound generated in a voiding process;

FIG. 12 depicts the ratios of measurement channel output to referencechannel output vs. time for the urine flow monitoring data shown in FIG.11; and

FIG. 13 presents the calibrated urine flow rate vs. time.

DETAIL DESCRIPTION OF PREFERRED EMBODIMENTS

As shown in FIG. 1, the medical urine flow monitoring device 2 includesa housing 4 that encloses a microphone 10, amplifier 12, a bank offilters 26 that includes filters 14, 16, 18, and 20, a signal processor22 and an output indicator 24. Electrical signals from microphone 10,which can be omnidirectional or unidirectional microphone(s), areamplified by amplifier 12 before being passed through a plurality offilters 14, 16, 18 and 20, that produce filtered signals 15, 17, 19, and21, respectively. As further described herein, the bank of filters 26serves to select the filtered signals of the desired frequency ranges tobe analyzed by processor 22. The filters comprise one or more of ahigh-pass, low-pass, band-pass, and band-stop filter, for example, whichare designated as Filters A, B, C and D, respectively. FIG. 1 depicts afour-channel urine flow-monitoring device with each channel employing adifferent type of filter. As further described herein, preferably one ormore of the channels measure sound level with frequencies in ameasurement range and one or more of the channels measure sound levelwith frequencies in a reference range. The choice of filters depends on,among other things, the filtered frequencies of interest. The filtersmay be fixed or variable. Housing 4 can be constructed as a portableunit that can secured to a person's belt or it can be designed as apermanent wall unit that can be mounted on the bathroom wall at home,the hospital or doctor's office.

FIG. 2 depicts a multiple channel urine flow-monitoring device thatincludes a microphone 10, amplifier 12, a bank of filters 28, a signalprocessor 22 and an output indicator 24. This embodiment illustrates adevice where multiple channels use the same type of filters, preferablywith different frequencies of operation, and is expected to be moreaccurate than the device of FIG. 1. Filters 30 and 32, which producefiltered signals 31 and 33, respectively, employ filters of type A.Filters 34 and 36, which produce filtered signals 35 and 37,respectively, employ filters of type B. And finally, filters 38 and 40,which produce filtered signals 39 and 41, respectively, employ filtersof type C.

FIG. 3 depicts a multiple channel urine flow monitoring device thatincludes a microphone 10, amplifier 12, a bank of filters 66, a signalprocessor 22 and an output indicator 24. This embodiment illustrates amultiple channel device that uses the same type of filters.Specifically, filters 42, 44, 46, and 48, which produce filtered signals43, 45, 47, and 49, respectively, each employs a filter of type A.

FIG. 4 depicts a multiple channel urine flow monitoring device thatincludes a microphone 10, amplifier 12, a bank of filters 86, a signalprocessor 22 and an output indicator 24. This embodiment illustrates adevice where at least one of the channels uses two or more filters.Specifically, amplified signals are passed through two channels: thefirst comprising filters 50, 52 and the second comprising filters 54,56, to produce filtered signals 53 and 57 that are processed byprocessor 22. Four different types of filters, designated A, B, C and D,are employed but it is understood different combinations of filters canbe used.

FIG. 5 depicts a multiple channel urine flow monitoring device thatemploys a microphone for each channel for improved performance. Eachmicrophone can be configured for sound acquisition in a particularfrequency range. Specifically the first channel includes microphone 70,amplifier 72 and filter 74; the second channel includes microphone 80,amplifier 82 and filter 84; and the third channel includes microphone90, amplifier 92 and filter 94. Processor 22 analyzes filtered signals75, 85, and 95 to generate programmed outputs that are displayed inindicator 24. Environment conditions such as pressure, temperature,humidity and other factors, such as urine receptacle geometry and sizeand water depth, that can influence the intensity and/or frequency ofthe sound detected are entered into processor 22. The patient's medicalhistory including his height, weight, blood pressure, bladder pressureand other health parameters can also be entered into the processor.

FIG. 6 depicts a urine flow monitoring device that includes a microphone160, amplifier 162, an analogue-to-digital converter 164, a signalprocessor 166 and an indicator 168. The analogue-to-digital converterconverts amplified microphone signal into digital form. The processordigitally filters the signal components of interest and generatesoutputs that are displayed by the indicator. As mentioned above,environment conditions and the patient's physical condition and medicalhistory can be entered into the processor.

FIG. 7 illustrates an embodiment of the medical urine flow monitoringdevice which is similar to that of FIG. 6 that incorporates a fastFourier transform (FFT) unit 186. Specifically, the device includes atransducer 180, such as a microphone, an amplifier 182,analogue-to-digital (A/D) converter 184, signal processor 188 andindicator/display unit 189. FFT 186 produces digital signalsrepresenting the data in a plurality of frequency ranges. These signalsin turn are processed by processor 188 that calculates various urineflow parameters, which are visually presented in indicator/display unit189. The device can also include memory 190 for storing raw digitizedsignals, spectrum information in the frequency ranges of interest,filtered signals, and calculated void process parameters.

Components that form the medical urine flow monitoring device of thepresent invention can be incorporated in a single integral unit or theycan be housed in separate stand-along peripherals or modules. Forexample, as shown in FIG. 8, the medical urine flow monitoring device202 includes a transducer 210, a data acquiring and processing unit(DAPU) 204, and output indicator/display unit 206. DAPU 204 includes anamplifier 212, analogue-to-digital (A/D) converter 213, a bank offilters that includes digital filters 214, 216, 218, and 220, and signalco-processor 222. Each digital filter can be selected from the groupconsisting of a high-pass, low-pass, band-pass, and band-stop filter,for example, which are designated as Filters A, B, C and D,respectively. While the bank of four filters is illustrated as havingfour different types of filters, it is understood that the filters canbe of the same type or different types. Transducer 210, such as amicrophone, converts sound to electrical signals that are amplified byamplifier 212. Output signals from amplifier 212 are converted intodigital signals by A/D converter 213 before being processed by theplurality of filters 214, 216, 218 and 220 that produce filtered signals215, 217, 219, and 221, respectively. The bank of filters serves toselect the filtered signals of the desired frequency ranges to beanalyzed by co-processor 222 which processes the filtered signals andcalculates the flow level and void process parameters, such as themaximum and average flow levels, time duration of urination frombeginning to its maximum level and total voided urine volume. Results ofthe calculations, including dynamic flow-time dependence data, arevisually presented in indicator/display unit 206, which can comprise alight-emitted diode, liquid crystal or other displays.

As an option, DAPU 204 can include memory 230 for storing raw digitizedsignals, filtered signals, and calculated void process parameters. Thestored information can be retrieved from the memory, processed throughthe filters and displayed as needed. The data can also be compared tothe latest test results to evaluate trends in the urine flow dynamics.The DAPU 204 can be constructed as a dedicated urine flow monitoringperipheral device that has a built-in microphone 210. Alternatively, themicrophone is housed in a separate audio peripheral device that can beoperatively coupled to the DAPU peripheral device via a cable or bywireless communication. FIG. 8 depicts the amplifier 212 and A/Dconverter 213 as being housed in the DAPU but it is understood that theamplifier or both the amplifier and A/D converter can be housed with themicrophone as part of the audio peripheral device. Likewise, theindicator/display can be housed together with the DAPU or all thecomponents of the urine flow monitoring device can be housed in a singlehousing.

The device of the present invention as illustrated in FIGS. 6, 7 and 8can employ, for instance, logarithmic or linear amplifiers. If the urineflow monitoring device has a logarithmic amplifier and is configured toprocess sound levels in decibels, its amplified signals are passedthrough the measurement and reference channel filters and the differencein the decibel readings is calculated, signal components are stored,analyzed, and converted by the co-processor's into signals for theindicator or display. It should be noted that in operation preferablyreadings are continuously derived from both the measurement andreference channels from the beginning to the end of the voiding process,stored and then processed to yield information about the patient's urineflow pattern and to provide an evaluation of the patient's condition.

In the case where the urine flow monitoring device has a linearamplifier and is configured to process sound levels in linear units, itsamplified signals are passed through the measurement and referencechannel filters and the ratios of the filtered signal readings arecalculated, signal components are stored, analyzed, and converted by theco-processor into signals for the indicator or display.

One method of calibrating the urine flow-monitoring device is to measurethe sound with the measurement channel and reference channel atdifferent urine flow rates under controlled flow conditions. Anothermethod is based on the total urine volume voided during the calibration.For example, as the flow impacts the water in a toilet, the urine flowmonitoring device captures the sound and records the corresponding soundlevels of the measurement channel M(t) and reference channel R(t). Theoutput signal, which is calculated as the difference between themeasurement and reference channels: D(t)=M(t)−R(t), and which isproportional to the flow rate is calibrated with respect to the totalurine volume V₀. It is known that the area under the function D(t)corresponds to the total urine volume V₀, which can be calculated by theequation V₀=∫_(t) ₁ ^(t) ² (A·D(t)+B)dt, where A and B are thecalibration coefficients, and t₁ and t₂ are times of the beginning andthe end of the urination process. Thus, calibrating the device onlyrequires that coefficients A and B be determined. If a linear amplifieris used, the total voided urine volume is calculated as V₀=∫_(t) ₁ ^(t)² (C·F(t)+D)dt, where F(t) is the ratio between measurement signal MO)and reference signal R(t): F(t)=M(t)/R(t), and C and D are thecalibration coefficients. Polynomial dependencies of the higher order,if needed, can also be used to calibrate the device. As is apparent, theurine flow-monitoring device can employ multiple measurement channelsand multiple reference channels and the output signals derived from eachdevice can be similarly calibrated.

Environmental conditions such as temperature and pressure can affectmeasurements of the urine-flow monitoring device. A device can becalibrated under different conditions at the factory so that when apatient uses the device he can set the appropriate operating conditionsof temperature, pressure etc. so that the correct calibration constantsare used.

The DAPU peripheral device can be connected to a display apparatus 206(FIG. 8) that is in the form of a portable computer that includes, forexample, a notebook, laptop, mobile computer, cell phone, smart phone,interne device, and the like. The connection between the DAPU andportable computer can also be through a cable using designated ports orby wireless technology. The DAPU output can be configured to be inanalogue or digital form consisting of raw or processed signals. Forexample, a smart phone can be equipped with the requisite softwareapplication to process and display test results.

FIG. 9 illustrates a portable apparatus for measuring urinary flowpatterns that includes an audio peripheral device that includes amicrophone and a processing peripheral device that includes a DAPU. Inthis embodiment, the audio peripheral includes a microphone that isembedded in the processing peripheral to form an integral unit. A smartphone is configured to receive signals from the DAPU. Themicrophone/DAPU assembly can be secured to an article of clothing suchas a belt. In operation, the DAPU acquires and process signals generatedduring a voiding process. The processed information is transmitted via“blue tooth” or other wireless protocol to the smart phonesimultaneously during the voiding process. Test results can be displayedimmediately after the voiding process or, being retrieved from thememory, at a later convenient time. In addition, the patient cantransmit the data from the smart phone to a data base, peripheralprinter, doctor's office, or other remote receiver.

It is contemplated that the DAPU can be incorporated into a smart phoneor other portable computer device, which can be programmed to acquire,filter and process sound information to generate urine flow dynamicsdata during voiding.

When a male patient urinates, a continuous, distinctive sound isproduced as the urine impacts the water in the toilet. Threerepresentative sound spectra captured by a microphone during urinationsare presented in FIG. 10. Spectrum 104 depicts the measured response inthe case where the urination exhibited “strong” volumetric flow,spectrum 106 was the response for “medium” volumetric flow, and spectrum108 was the response for “weak” volumetric flow. As is apparent, thesound level signal in the frequency range of 250-550 Hz, which isdesignated a measurement range, strongly depends on a flow level,whereas the sound level signals in the frequency ranges of 1000-1200 Hz,2000-2200 Hz, and 4400-4600 Hz, which are designated as referenceranges, are significantly less so. Thus, by monitoring the loudness ofthe sound caused by urination at a frequency where the measured soundlevel depends on the flow level, it is possible to measure the urineflow rate. The intensity of the sound that is acquired by the microphoneis influenced by a number of extraneous factors including the relativeposition and distance of the microphone to the site of impact as well asenvironmental conditions. Thus, in a preferred embodiment, the urineflow monitoring device has at least two channels: one or moremeasurement channels that measures sound at a frequency within the rangeof 250-550 Hz and one or more reference channels that measures sound ata frequency within the range of 1000-1200, Hz 2000-2200 Hz, and/or4400-4600 Hz. As described further herein, by analyzing the differencebetween the decibel values of the measurement and reference signals orthe ratio between the measurement and reference signals, the urine flowrate and other data can be determined in a manner wherein measurementvariations caused by the extraneous factors are significantly reduced oreliminated. The urine flow-monitoring device can use one or more of thereference ranges.

A urine flow monitoring device consisting of a transducer device thatwas coupled to a laptop personal computer, which was configured toperform digital filtering on raw data, was used to monitor urine flowand its dynamics. Specifically, a transducer assembly, which included amicrophone, amplifier and A/D converter, was connected to computer via aUSB connector. The computer included customized software program(LabVIEW from National Instruments of Austin Tex.) that performeddigital filtering of microphone signals at measurement and referencefrequencies and their processing. The measurement and reference filterswere programmed as band pass filters with the range of 250-450 Hz forthe measurement channel and 1000-1200 Hz for the reference channel 1 and2000-2200 Hz for the reference channel 2. The computer also displayedthe test results.

To demonstrate device repeatability and the inventive technique'sindependence from the loudness of the voiding process, the sound patterngenerated by a male urinating into the water in a toilet was recorded.Thereafter, the same recorded sound pattern was reproduced repeatedly insuccession at four different loudness levels for analysis with the urineflow monitoring device. The output signals as measured by measurementchannel and reference channels 1 and 2 for each of the four runs areshown in FIG. 11. The loudness level for the second (and highest) soundpattern was about nine times that of the third (and lowest) soundpattern. Thereafter, the ratio of the output signals from themeasurement channel and reference channel 1 (designated as ratio 1) andthe output signals from the measurement channel and reference channel 2(designated as ratio 2) were calculated during the voiding and arepresented in the FIG. 12. As is evident, the contours of thedependencies for all four samples are very similar and their amplitudesare very similar as well.

The device was calibrated based on the total void urine volume which wasabout 380 mL. Calibration was applied to the average flow ratio, whichwas calculated based on ratio 1 and ratio 2 presented in FIG. 12.Calibrated urine flow level dependencies for each of the four runs arepresented in FIG. 13. As is apparent, the four dependencies areextremely close to each other. This demonstrates that the feature of theinvention of employing the ratio between measurement and referencechannels effectively eliminates the dependence on the loudness of themonitoring voiding process and position of the microphone. Thissignificantly increases reliability and accuracy of the measurement. Asis evident from the graph, the maximum flow rate was between 19 mL/secand 20 mL/sec and occurred approximately 11 to 12 seconds into theurination process. The average urine flow rate was about 9.2 mL/sec.

The urine-flow monitoring device can be programmed with data to enablethe unit to display urinary flow information, based on analysis andclassification, for the user. For example, analysis of the filteredsignals can yield information concerning the patient's voiding patterns,including: flow dynamics, maximum urine flow rate (which may beindicative of the level of urinary tract blockage, if any), averageurine flow rate, and time to maximum flow level. The filtered signalscan be correlated to urine flow levels. In order to customize thisinformation, the patient's height, weight, body mass index, bloodpressure and other data of his medical history can be uploaded into theprocessor. A database of urine flow data generated by patients who areclassified a being healthy as well as from those who are suffering fromvarious conditions that result in abnormal urine flow can be stored inthe processor's calibration circuit. Once a patient's voiding patternsare established with the device, they can be compared to voidingpatterns in the database and appropriate information displayed.

The foregoing has described the principles, preferred embodiment andmodes of operation of the present invention. However, the inventionshould not be construed as limited to the particular embodimentsdiscussed. Instead, the above-described embodiments should be regardedas illustrative rather than restrictive, and it should be appreciatedthat variations may be made in those embodiments by workers skilled inthe art without departing from the scope of present invention as definedby the following claims.

What is claimed is:
 1. An apparatus for measuring urine flow thatcomprises: a microphone for detecting acoustical sound that is generatedas urine impacts a liquid surface and converting it into electricalsignals; an amplifier operatively coupled to the microphone to amplifyelectrical signals therefrom; an analogue-to-digital converter forconverting electrical signals into digital form; a digital filteroperatively coupled to the analogue-to-digital converter for extractingfiltered signals; and a signal processor for analyzing filtered signalcomponents to generate urine flow level data.
 2. The apparatus of claim1 further comprising an electronic memory for storing the urine flowlevel data.
 3. The apparatus of claim 1 comprising a plurality ofmeasurement channels.
 4. The apparatus of claim 3 wherein eachmeasurement channel includes a plurality of digital filters.
 5. Theapparatus of claim 1 comprising a plurality of microphones.
 6. Theapparatus of claim 1 wherein the signal processor yields urine flow datathat is selected from the group consisting of average flow rate, maximumflow rate, time to maximum flow level, flow dynamics, and combinationsthereof.
 7. The apparatus of claim 1 further comprising means totransmit the urine flow data to a remote receiver.
 8. The apparatus ofclaim 1 further comprising means to transmit the urine flow data to adisplay means to generate a visual representation of the data.
 9. Theapparatus of claim 1 wherein extracted filtered signals from the digitalfilter comprise a measurement signal that is sensitive to urine flowlevel.
 10. The apparatus of claim 9 comprising two or more measurementchannels.
 11. The apparatus of claim 9 wherein the filtered signalscomprise measurement signals that have frequencies in the range from 250to 550 Hz.
 12. The apparatus of claim 1 wherein the filtered signalscomprise reference signals that are insensitive to urine flow level. 13.The apparatus of claim 12 comprising two or more reference channels. 14.The apparatus of claim 13 wherein the reference signals have frequenciesin the range from 1000 to 1200 Hz, 2000 to 2200 Hz, and/or 4400 to 4600Hz.
 15. A device for measuring urine flow that comprises: a transducerfor detecting acoustical sound that is generated as urine impacts aliquid surface and converting it into electrical signals; an amplifierto amplify the electrical signals; an analogue-to-digital converter forconverting the electrical signals into digital form; a digital filterfor extracting filtered signals; and means for analyzing signalcomponents to generate urine flow level data.
 16. The device of claim 15further comprising a transmitter to transmit signals, which arerepresentative of urinary flow data, for remote recording and assess.17. The device of claim 15 further comprising an indicator to displaythe urinary flow data.
 18. The device of claim 15 further comprisingelectronic memory for storing the urine flow level data.
 19. A systemfor analyzing urinary flow patterns of a male patient as he voids thatcomprises: a transducer for converting acoustic energy, that isgenerated as urine from the patient impacts a surface, into electricalsignals; an amplifier operatively coupled to the transducer to amplifyelectrical signals therefrom; an analogue-to-digital converter forconverting the electrical signals into digital form; a digital filteroperatively coupled to the analogue-to-digital converter for extractingfiltered signals; and means for analyzing signal components to identifyurinary flow patterns.
 20. The system of claim 19 comprising a pluralityof measurement channels.
 21. The system of claim 20 wherein eachmeasurement channel includes a plurality of digital filters.
 22. Thesystem of claim 19 comprising a plurality of microphones.
 23. The systemof claim 19 wherein extracted filtered signals from the digital filtercomprise a measurement signal that is sensitive to urine flow level. 24.The system of claim 23 wherein the filtered signals comprise measurementsignals that have a frequency in the range from 250 to 550 Hz.
 25. Thesystem of claim 19 wherein the filtered signals comprise referencesignals that are insensitive to urinary flow levels.
 26. The system ofclaim 25 wherein the filtered reference signals have frequencies in therange from 1000 to 1200 Hz, 2000 to 2200 Hz, and/or 4400 to 4600 Hz. 27.The system of claim 19 wherein the means for analyzing signal componentsyield urine flow data that is selected from the group consisting ofaverage flow rate, maximum flow rate, time to maximum flow level, flowdynamics, and combinations thereof.
 28. A portable apparatus formeasuring urinary flow patterns that comprises: (a) an audio peripheralthat comprises: a transducer for converting acoustic energy, that isgenerated as urine from a patient impacts a surface, into electricalsignals; and an amplifier operatively coupled to the transducer toamplify electrical signals therefrom; (b) an analogue-to-digitalconverter for converting the electrical signals into digital form; and(c) a processing peripheral that comprises: a digital filter operativelycoupled to the analogue-to-digital converter for extracting filteredsignals; and means for processing signal components to generate signalsthat are representative of urinary flow data, wherein theanalogue-to-digital converter is housed in the audio peripheral or inthe process peripheral.
 29. The portable device of claim 28 wherein theaudio peripheral and processing peripheral form an integral unit. 30.The portal device of claim 28 wherein the audio peripheral andprocessing peripheral are separate units wherein the processingperipheral module is a portable computer.
 31. The portable device ofclaim 28 wherein the processing peripheral has an indicator to displaythe urinary flow data.
 32. The portable device of claim 28 wherein themeans for processing signal components yield urine flow data that isselected from the group consisting of average flow rate, time to maximumflow level, maximum flow rate, time to maximum flow level, flowdynamics, and combinations thereof.
 33. A method for measuring urinaryflow from a male patient as he voids that comprises the steps of: (a)detecting acoustic energy that is generated as urine impacts a liquidsurface; (b) converting the acoustic energy into electrical signals; (c)converting the electrical signals into digital form; (d) extractingfiltered signals from the electrical signals in digital form with adigital filter; and (e) processing the filtered signals, togenerate-output signals that represent urinary flow data for the malepatient.
 34. The method of claim 33 wherein step (d) comprisesseparating the electrical signals in digital form into spectralcomponents of various frequencies before the spectral components areprocessed in step (e).
 35. The method of claim 34 wherein a firstspectral component has a frequency in the range of 250 to 550 Hz and asecond spectral component has a frequency in the range of 1000 to 1200Hz, 2000 to 2200 Hz, and/or 4400 to 4600 Hz.